Adjustable spinal implant

ABSTRACT

In one embodiment, a non-invasively adjustable spinal system for treatment of a subject having spondylolisthesis includes a first implantable actuator having at least one anchoring structure, the anchoring structure configured to facilitate securement of the first implantable actuator to a portion of the sacrum of the subject. The non-invasively adjustable spinal system can further include an adjustment element, configured to be coupled to the first implantable actuator, the adjustment element having an engagement structure configured to engage at least one transverse process of a lumbar vertebra of the subject. The non-invasively adjustable spinal system can further include a driving element, wherein remote activation of the driving element causes movement of the adjustment element in relation to the first implantable actuator.

INCORPORATION BY REFERENCE TO ANY PRIORITY APPLICATIONS

Any and all applications for which a foreign or domestic priority claims is identified in the Application Data Sheet as filed with the present application are hereby incorporated by reference under 37 CFR 1.57.

BACKGROUND Field of the Invention

The field of the invention generally relates to medical devices for treating deformities of the spine, including spondylolisthesis.

Description of the Related Art

Spondylolisthesis is a condition of the spine in which one vertebra is displaced in relation to another vertebra.

SUMMARY

In one embodiment, a non-invasively adjustable spinal system for treatment of a subject having spondylolisthesis is provided. The system includes a first implantable actuator having at least one anchoring structure, the anchoring structure configured to facilitate securement of the first implantable actuator to a portion of the sacrum of the subject. The non-invasively adjustable spinal system further includes an adjustment element, configured to be coupled to the first implantable actuator, the adjustment element having an engagement structure configured to engage at least one transverse process of a lumbar vertebra of the subject. The non-invasively adjustable spinal system further includes a driving element, wherein remote activation of the driving element causes movement of the adjustment element in relation to the first implantable actuator.

In another embodiment, a method for treating spondylolisthesis in a subject having a spine containing a sacrum and at least a portion of an L5 vertebra is provided. The method includes providing a non-invasively adjustable spinal implant having a first implantable actuator having at least one anchoring structure, the anchoring structure configured to facilitate securement of the first implantable actuator to a portion of the sacrum of the subject, an adjustment element, configured to be coupled to the first implantable actuator, the adjustment element comprising an engagement structure configured to engage at least one transverse process of a lumbar vertebra of the subject, and a driving element, wherein remote activation of the driving element causes movement of the adjustment element in relation to the first implantable actuator. The method for treating spondylolisthesis further includes making a first incision in the skin of the subject, placing the non-invasively adjustable spinal implant through the first incision, securing at least a portion of the non-invasively adjustable implant to a portion of the sacrum of the subject, coupling the engagement structure to at least one transverse process of the L5 vertebra, and causing or allowing the first incision to close.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A illustrates three lower lumbar vertebra and sacrum of a spine.

FIG. 1B illustrates a lower spine exhibiting the condition of spondylolysis in the L5 vertebra.

FIG. 1C illustrates a lower spine exhibiting the condition of spondylolisthesis between the L5 vertebra and sacrum.

FIG. 2A is a partial sectional view of a normal portion of a lower spine.

FIG. 2B is a partial sectional view of a lower spine exhibiting Grade I spondylolisthesis.

FIG. 2C is a partial sectional view of a lower spine exhibiting Grade II spondylolisthesis.

FIG. 2D is a partial sectional view of a lower spine exhibiting Grade III spondylolisthesis.

FIG. 2E is a partial sectional view of a lower spine exhibiting Grade IV spondylolisthesis.

FIG. 2F is a partial sectional view of a lower spine exhibiting Grade V spondylolisthesis.

FIG. 3A illustrates a spinal column of a subject.

FIG. 3B illustrates an orientation of a sacrum of the spine of a subject.

FIG. 4 is a perspective view of a lower spine of a normal subject.

FIG. 5 is a perspective view of a lower spine of a subject having spondylolisthesis.

FIG. 6 illustrates a dorsal portion of a sacrum of a subject.

FIG. 7 illustrates an adjustable spinal implant according to an embodiment of the present invention.

FIG. 8 illustrates a side view of the adjustable spinal implant of FIG. 7.

FIG. 9 illustrates the adjustable spinal implant of FIG. 7 with certain external components removed.

FIG. 10 illustrates a magnetic actuator.

FIG. 11 is a cross-sectional view of the magnetic actuator of FIG. 10 taken along the line 11-11.

FIG. 12 illustrates a maintenance tube of the magnetic actuator of FIG. 10.

FIG. 13 illustrates certain components of an adjustable spinal implant in a first adjustment condition.

FIG. 14 illustrates certain components of an adjustable spinal implant in a second adjustment condition.

FIG. 15 illustrates a connectable interface between a magnetic actuator and a gear housing.

FIG. 16 illustrates the adjustable spinal implant of FIG. 7 implanted on a spine of a subject having spondylolisthesis.

FIG. 17 illustrates a side view of an adjustable implant implanted on a spine of a subject having spondylolisthesis.

FIG. 18 illustrates a spine of a subject having spondylolisthesis after reduction treatment by an adjustable spinal implant.

FIG. 19 illustrates a side view of adjustable spinal implants according another embodiment of the present invention implanted on a spine of a subject having spondylolisthesis.

FIG. 20 illustrates a spine of a subject having spondylolisthesis after reduction treatment by adjustable spinal implants.

FIG. 21 illustrates a perspective view of an external adjustment device.

FIG. 22 illustrates an exploded view of a magnetic handpiece of the external adjustment device of FIG. 21.

FIG. 23A illustrates a magnetic actuator of an adjustable spinal implant according to an embodiment of the present invention during removal of a magnetic assembly.

FIG. 23B illustrates a magnetic actuator of an adjustable spinal implant after removal of a magnetic assembly.

FIG. 23C illustrates a magnetic actuator of an adjustable spinal implant after replacement of an actuator housing cap.

FIG. 24A illustrates a magnetic actuator of an adjustable spinal implant according to an embodiment of the present invention prior to removal of a radially-poled permanent magnet.

FIG. 24B illustrates a magnetic actuator of an adjustable spinal implant during removal of a radially-poled permanent magnet.

FIG. 24C illustrates a magnetic actuator of an adjustable spinal implant after removal of a radially-poled permanent magnet and replacement of a magnetic housing cap.

FIG. 24D illustrates a magnetic actuator of the adjustable spinal implant after replacement of an actuator housing cap.

FIG. 25 illustrates an adjustable spinal implant according another embodiment of the present invention implanted on the spine of a subject with spondylolisthesis.

FIG. 26 illustrates a sectional view of the adjustable spinal implant of FIG. 25.

FIGS. 27-30 schematically illustrate various embodiments of alternate sources of a driving element of a non-invasively adjustable spinal implant.

DETAILED DESCRIPTION

In FIG. 1 the lower spine 100 includes vertebrae L3 102, L4 104, L5 106, and the sacrum 108. Intervertebral discs 110, 112, 114 are also shown. In certain subjects, chronic or acute upward stresses on the sacrum 108 can create upward forces on the contacting spinous process 116 (in this case the spinous process 116 of L5 106) and downward forces on the L5 106 vertebral body itself. This may culminate in a defect 120, for example, a stress fracture, of the pars interarticularis 118. The defect 120, as seen in FIG. 1B, is known as spondylolysis, and may occur in as much as 6% of the population. Some risk factors which may lead to spondylolysis, often occurring in combination, include hereditary anatomic factors (thin spinal bone) and strenuous sports and activities, such as tennis, volleyball, soccer, and gymnastics. The hyperextension and heavy landings common to many strenuous sports have each been hypothesized as causes for spondylolysis. The L5 106 vertebra is the location of the defect 120 in the majority of spondylolysis cases, but it may also occur in other lumbar vertebrae, and even in non-lumbar vertebrae. Spondylolysis may on its own cause back pain, neck pain, or radiating limb pain, but it is often followed by related disc slippage known as spondylolisthesis, which is illustrated in FIG. 1C. The spondylolisthesis in FIG. 1C is shown between the L5 106 vertebra and the sacrum 108. This is thought to be the most common location for spondylolisthesis to occur, but again, it may occur between other vertebrae.

In many people, the defect 120 is created during adolescence, but it often goes unnoticed at that time. Typical disc degeneration occurring during adulthood may then produce the spondylolisthesis, which can be accompanied by other symptoms. Sometimes, adult degenerative disc disease may even lead to spondylolisthesis without the defect 120 (spondylolysis) occurring. FIG. 2A illustrates the L4 104 and L5 106 of the lumbar vertebrae and S1 122, S2 124, and S3 126 vertebrae of the sacrum 108 of a subject having L5-S1 segment 128 which is normal. FIGS. 2B through 2F show L5-S1 segments 128 having increasing grades of spondylolisthesis. These figures are intended to show the orientation of the L5 106 to the S1 122, and not their overall orientation in relation to anything else, for example, the ground while the subject is standing. A commonly used method of grading spondylolisthesis divides the sacrum 108 into four equal sectors (i.e., 1, 2, 3, and 4), as seen in FIG. 2A. A subject has a grade 1 spondylolisthesis (FIG. 2B) when the edge 130 of the slipped vertebra (in this case L5 106) is within sector 1. In FIG. 2C the spondylolisthesis is grade 2 because the edge 130 of the slipped L5 106 is within sector 2. In FIG. 2D the spondylolisthesis is grade 3 because the edge 130 of the slipped L5 106 is within sector 3. In FIG. 2E the spondylolisthesis is grade 4 because the edge 130 of the slipped L5 106 is within sector 4. In FIG. 2F the edge 130 of the slipped L5 106 has slipped past the four sectors and is therefore considered a grade 5; the condition of grade 5 spondylolisthesis is also known as spondyloptosis. In the higher grades of spondylolisthesis, subjects may either remain asymptomatic, or may present with back pain and/or leg pain. Subjects having higher grade spondylolisthesis may also experience secondary changes to the natural sagittal curve of their spine (sagittal deformity). It may be desirable to treat an adult who has experienced chronic pain symptoms that may be medically attributed to a spondylolisthesis grade of about 4 or higher by implantation of an embodiment of devices as described and illustrated herein. Such treatment may be used to either minimize the risk of progression to a higher spondylolisthesis grade, to lower the spondylolisthesis grade, or both minimize the risk of progression and lower the grade of spondylolisthesis.

Adolescents with higher grade spondylolisthesis may be at a heightened risk for progression in the severity of their condition than adults, and for this reason, surgery is often recommended. While adults with spondylolisthesis may have less risk of progression, they often have back pain or leg pain symptoms that warrant surgery. In order to reduce the risk of progression to a higher grade spondylolisthesis it may be desirable to treat an adolescent having grade 1 spondylolisthesis that is at risk of progressing/worsening by implantation of an embodiment of devices as described and illustrated herein.

FIGS. 3A and 3B illustrate several sagittal pelvic parameters which may be calculated from x-rays (taken while the subject is standing) in subjects having L5-S1 spondylolisthesis, or at risk of progression of L5-S1 spondylolisthesis. The purpose of these parameters is to describe the location and orientation of the sacrum 108 in relation to the ground and to the entire spinal column 144 and pelvis. Lumbar lordosis (LL) 132 is defined as the angle measured between the superior (upper) endplate of the L1 vertebra 134 and the superior endplate of the S1 vertebra 122. Thoracic vertebra T12 136 is also shown in FIG. 3A, for reference. Pelvic tilt (PT) 138 is defined as the angle between vertical 146 (a line perpendicular to the ground on which the subject stands) and the line 148 which leads to the middle 150 of the sacral plate 152 at the superior end of the sacrum 108 (chosen midline between the two hip/femur joints). Sacral slope (SS) 140 is defined as the angle between the horizontal 154 and a line 156 drawn along the sacral plate 152 at the superior end of the sacrum 108. Pelvic Incidence (PI) 142 is equal to the sum of the pelvic tilt (PT) 138 and the sacral slope (SS) 140. Some studies have concluded that an increased pelvic incidence (PI) 142 may be a risk factor for the development and progression of spondylolisthesis.

Surgery typically includes of partial or complete reduction (restoration to correct alignment) followed by fusion, or, in many cases, fusion alone without reduction. Fusion without reduction (in situ fusions) can be successful in subjects in whom symptoms have occurred mainly because of motion of the segment. However, in a large number of subjects, some amount of reduction prior to fusion can advantageously decompress the nerve root. Reduction of higher grade spondylolisthesis may be difficult due to both increased rigidity of the deformity and stiffness across the junction between the L5 106 and S1 122. This is especially true in adults who have secondary degenerative changes as the entire deformity is frequently less mobile. In some studies, a significant percentage of subjects experienced further slip progression, even after fusion surgery, a phenomenon that some attribute to incomplete correction of the angular deformity (e.g., bringing the lumbar lordosis (LL) 132 back towards its normal desired value). Fusion without reduction may also be associated with higher rates of non-union than reduction followed by fusion, which many have attributed to the higher stresses on the junction between the L5 106 and S1 122, and also to the decreased surface area for fusion because of the incomplete alignment of the L5 106 and S1 122.

FIGS. 4 and 5 depict the lower spine 100 of a normal subject (FIG. 4) and a subject with spondylolisthesis (FIG. 5). In FIGS. 4 and 5, the lower spine 100 is shown without the surrounding soft tissue in order to better illustrate a treatment plan using an embodiment of devices as described and illustrated herein. An adjustable spinal implant 200 (FIG. 7) according to an embodiment of devices as described and illustrated herein will be coupled at least partially to a medial-dorsal portion 158 of the sacrum 108 following removal of a dorsal portion 160 of the L5 106, for example, a dorsal portion 160 that previously had been severed from the L5 106 during the creation of the defect 120 in spondylolysis. FIG. 6 illustrates the anatomy of a dorsal portion of the sacrum 108, indicating the medial-dorsal portion 158 within a dashed box. Within this medial-dorsal portion 158 is the sacral crest 162 which covers the sacral canal 174 and extends towards the sacral hiatus 170. The sacral crest 162 comprises a plurality of tubercles 172. Several dorsal sacral foramina 164 (also called posterior sacral foramina) are arrayed along the sacrum 108 and provide openings in the sacrum 108 for the transmission of the posterior divisions of the sacral nerves (not shown). Two alas 166 extend laterally and two sacral horns 168 (also called superior auricular processes) reside at the superior portion of the sacrum 108. A medial surface 176 (within the dashed oval marking) at the edge of each ala 166 extends substantially towards each sacral horn 168. The adjustable spinal implant 200 of FIG. 7 may also be configured to at least partially contact a portion of the medial surface 176.

The reason that reduction is sometimes avoided prior to fusion is traditionally because it is often associated with a high rate of neurological deficit. However, neurological deficit can also occur, though at a lower rate, in fusions done without reduction. Because of complications inherent to either excess reduction or insufficient reduction, a partial reduction prior to fusion may elicit the best result. However, it is frequently difficult to predict what will be the most appropriate amount of reduction prior to fusion. Additionally, a gradual reduction, such as several small steps spaced out by days, weeks or even months, may allow for a complete reduction prior to fusion: in some cases, it may even obviate fusion.

FIGS. 7 and 8 illustrate an adjustable spinal implant 200 for implantation and subsequent non-invasive adjustment within a subject having spondylolisthesis. The adjustable spinal implant 200 comprises an implantable actuator 204 which is coupled to an adjustment element 206. Between the implantable actuator 204 and the adjustment element 206 is a flexible tubular member 218, which serves to protect the connecting elements and create a seal or barrier to prohibit body fluids from entering either the implantable actuator 204 or the adjustable element 206. The implantable actuator 204 includes an anchoring structure 208, for example, anchoring tabs 210 having holes 212 for passing bone screws to secure the implantable actuator to the sacrum 108 of a subject. The adjustment element 206 comprises a gear housing 214 which is fully enclosed by a gear housing cover 216. The adjustment element 206 also includes an engagement structure 220 having a right transverse process hook 222 and a left transverse process hook 224. The engagement structure 220 may be monolithic or may be an assembly of more than one part. The engagement structure 220 is adjustable with respect to the gear housing 214. A moveable arm 236 of the engagement structure 220 extends into the gear housing 214. A dynamic seal 234 is provided in an opening 238 of the gear housing 214, which seals around the moveable arm 236. The adjustment element 206 includes several feet 226, 228, 230, 232 which aid in stabilizing the adjustment element 206 with respect to the sacrum 108 by, for example, providing opposing forces to traction created when the engagement structure 220 is adjusted.

FIGS. 9 through 15 show additional internal and external detail of the adjustable spinal implant 200. FIG. 9 shows the adjustable spinal implant 200 with the flexible tubular member 218 and the gear housing 214 removed. A driving element or rotatable magnetic assembly 242 is rotationally mounted within a housing 205 of the implantable actuator 204 and comprises a radially-poled permanent magnet 202 which is held within a magnetic housing 240, for example, with adhesive or epoxy, or by a mechanical fit. The magnetic housing 240 sealably encloses the radially-poled permanent magnet 202 by attachment of a magnetic housing cap 244. The radially-poled permanent magnet may be a cylindrical or partially cylindrical rare earth magnet, for example, Neodymium-Iron-Boron, and may have two poles, four poles, or more. The rotatable magnetic assembly 242 is coupled to a planetary gear set 246, and both the rotatable magnetic assembly 242 and the planetary gear set 246 are held between a radial bearing 248 and a thrust bearing 250. The output shaft 252 of the planetary gear set 246 is joined to a rotational coupler 254, for example, by welding or adhesive bonding. If, for example, the planetary gear set 246 is provided with a 4:1 gear ratio, then four rotations of the rotatable magnetic assembly 242 cause one rotation of the rotational coupler 254. Additionally, given a 4:1 gear ratio, torque generated by the rotational coupler 254 can be up to four times greater than the torque applied to the radially-poled permanent magnet 202 (for example, by the application of a rotating magnetic field). An o-ring 256 is held within a circumferential groove 258 in the housing 205, and seals around the diameter of the rotational coupler 254.

A universal joint 258 (FIG. 9) provides a flexible connection between the rotational coupler 254 and a worm 260. FIG. 15 illustrates the releasable connection between the implantable actuator 204 and the adjustable element 206. A first member 262 of the universal joint 258 having a square end 264 can be snapped into and snapped out of a square cavity 266. The universal joint 258 and the surrounding flexible tubular member 218 allow for the securement of both the implantable actuator 204 and the adjustable element 206 in a number of different orientations, to match varying anatomy of the subject, while still allowing operation. The worm 260 engages a worm gear portion 268 of a gear 270 so that rotation of the worm 260 causes rotation of the gear 270. As visible also in FIGS. 13 and 14, the gear may also include a pinion 272 configured to engage with an arcuate rack 274 that extends from the movable arm 236 of the engagement structure 220. As the gear 270 is caused to turn in a first rotational direction by the worm 260 the arcuate rack 274 moves in an arcuate path 276. By providing an engagement structure 220 capable of holding the L5 vertebra 106 without any rotational slippage, the L5 vertebra 106 may not only be translated (reduced) in relation to the sacrum 108, but also, the L5 vertebra 106 may be rotated (or derotated) in relation to the sacrum 108. An example is shown by the decrease of angle A from FIG. 13 to FIG. 14, which happens in conjunction with the displacement of right transverse process hook 222. Such angle change can lower the pelvic incidence (PI) 142 in a subject, and thus potentially lower their risk of progressive spondylolisthesis. Angle change can also directly improve lumbar lordosis (LL) 132. One way of achieving this change in angle of the L5 vertebra 106 is shown in FIG. 9. A cross bar 278 extends between the right transverse process hook 222 the left transverse process hook 224, and is configured to provide a pushing force in the proximity of a dorsal portion of the L5 vertebra 106 while the right transverse process hook 222 the left transverse process hook 224 are providing traction. Because these opposing forces are applied at different heights on the L5 vertebra 106 (one inferior to the other), a rotational moment is applied to the L5 vertebra 106. The gear 270 and the worm 260 are held within both the gear housing 214 and the gear housing cover 216 by standard stops, pins, bosses and the like. Additionally first bar 290 and second bar 292 extend within the gear housing 214 and/or the gear housing cover 216 in order to act as guides for the arcuate rack 274 as it is moved. At least the second bar 292 can act as a stop to prevent overextension of the arcuate rack 274.

The housing 205 of the implantable actuator 204 may also contain a maintenance tube 280 (illustrated in FIG. 12). The maintenance tube 280 is constructed from a structurally rigid material that is also relatively magnetic, for example, 400 series stainless steel. Open elongated holes 282 in the wall of the maintenance tube 280 cause circumferential magnetic discontinuities. The north and south poles of the radially-poled permanent magnet 202 will be attracted to the extending wall ribs 284, but not to the open elongated holes 282. While implanted within a subject, the adjustable spinal implant 200 maintains its configuration (dimension, etc.) due to this attraction. Adjusting the adjustable spinal implant 200 with the use of a sufficient strong externally applied moving magnetic field can overcome this attraction and allow the radially-poled permanent magnet 202 to be turned. The maintenance tube 280 is secured within the housing 205 of the implantable actuator and can provide one end of an axial stop for the thrust bearing 250. Another axial stop for the thrust bearing 250 can be provided by a ledge 286 within the housing 205. In some embodiments, the thrust bearing 250 is not held completely tight, and may have a finite amount of axial play. In other embodiments, the thrust bearing 250 is held with substantially no axial play. An actuator housing cap 288 may be permanently or removably attached to the housing 205 of the implantable actuator 204 to enclose and protect the contents of the housing 205 from body fluids.

In use, the adjustable spinal implant 200 can be coupled to the L5 vertebra 106 and the sacrum 108 by a surgeon during a surgical implantation procedure. The adjustable spinal implant 200 is shown in FIG. 16, as implanted, on the L5 vertebra 106 and sacrum 108. The right transverse process hook 222 of the engagement structure 220 has been hooked around a right transverse process 178 of the L5 vertebra 106. The left transverse process hook 224 of the engagement structure 220 has been hooked around a left transverse process 180 of the L5 vertebra 106. A foot 226 has been trimmed and/or bent (or otherwise shaped) so that it rests against medial surface 176 of the right ala 166 and a foot 228 has been trimmed and/or bent (or otherwise shaped) so that it rests against medial surface 176 of the left ala 166. The implantable actuator 204 has been secured to the sacrum 108 by placing bone anchors 294 through the holes 212 in the anchoring tabs 210 (shown in FIG. 7). The bone anchors 294 may comprise a screw having a threaded shank and a tapered threaded head. The holes 212 may have matching tapered internal threads to interface with the tapered head of the bone anchors 294. The adjustable element 206 has been coupled to the implantable actuator 204 via the square end 264 and square cavity 266, and the flexible tubular member 218 has been slid into place over the end of the housing 205 of the implantable actuator 204 and over a cylindrical extension (not shown) of the gear housing 214. It can be appreciated from FIG. 17 that legs 230, 232 may also be trimmed and/or bent (or otherwise shaped) to contact medial-dorsal portion 158 of the sacrum 108. Prior to the implantation of the adjustable spinal implant 200, portions of the sacral crest 162 and other bone material within the medial-distal portion 158 may be cut or ground away, or even partially hollowed out. As can be seen in FIGS. 16 and 17, the implantable actuator 204 may reside partially within this hollowed out area.

In FIGS. 16 and 17, the L5 vertebra 106 is in a slipped position approximating grade 3 spondylolisthesis in relation to the sacrum 108. FIG. 17 shows the lower spine 100 after a dorsal portion 160 of the L5 vertebra 106 has been removed through an incision in the skin. Subsequently, the adjustable spinal implant 200 is implanted as described above and the incision is allowed or caused to close, for example, by suturing or using an adhesive sealant, and the overall healing is allowed to progress. In one or more subsequent procedures, a medical care professional or a member of the family of the subject applies a remote moving magnetic field, thereby causing the moveable arm 236 to be retracted into the gear housing 214 via the rack 274 and pinion 272. FIG. 18 shows the lower spine 100 after one or more adjustment procedures. The L5 vertebra 106 has been reduced to a position approximating grade 1 spondylolisthesis. In addition, the angular orientation between the L5 vertebra 106 and the sacrum 108 has been changed. Specifically, the kyphotic condition has been improved, returning more of the natural lordosis. Because the lumbar vertebrae are connected to each other, the reduction of the L5 vertebra 106 may cause the lower spine 100, particularly the adjacent L4 vertebra 104 and L3 vertebra 102, to reform to its preferred conformation. It should be noted that in FIGS. 17 and 18, the foot 226 has purposely not been depicted to better show the positioning of feet 230 and 232.

It may be useful to perform the adjustment of spondylolisthesis using the adjustable spinal implant 200 on a conscious subject who is able to provide at least substantially real-time feedback related to pain and/or balance. Conscious subjects may be able to advantageously move into several different, positions, including those positions that are most likely to cause pain. This is to be contrasted with “wake up tests,” sometimes performed during surgery, in which subjects are neither in natural positions, nor do they have their standard senses and reflexes (due to the effects of drugs and anesthesia). Additionally, the amount of linear reduction to treat a patient is generally expected to be in the range of about 5-60 mm, about 7-50, and more specifically about 10-40 mm. Derotation of the L5 vertebra 106 in relation to the sacrum 108 versus the total amount of linear reduction can be controlled by producing a rack having varied radii. For example, a straight (linear) rack may be used if no derotation is desired. It is generally expected that derotation in the range of about 0-75 degrees is appropriate, and in many cases a derotation in the range of about 5-50 degrees. The amount of adjustment may be at least partially determined using feedback received from a conscious subject.

FIGS. 19 and 20 depict a pair of adjustable spinal implants 300, 400 according to another embodiment of the of devices as described and illustrated herein. A first adjustable spinal implant 300 comprises a first implantable actuator 304 coupled to a first adjustable element 306, with a flexible tubular member 318 extending between them. The first implantable actuator 304 may be secured to the sacrum by a bone anchor 294 which passes through an anchoring tab 310. In some embodiments, only one anchoring tab 310 is used, with the other removed, leaving a remnant 311. In other embodiments, two anchoring tabs 310 are used. A right transverse process hook 322 is hooked around the right transverse process 178. A stability element 313 is secured to the right transverse process hook 322 with a set screw 315, in order to clamp onto the right transverse process 178 and substantially eliminate rotational slippage between the right transverse process hook 322 and the right transverse process 178. The surface of the right transverse process 178 may be slightly ground flat in order to better accept the stability element 313 to further inhibit rotation between the two. The right transverse process hook 322 may be directly connected to a movable arm 336 which extends into a rack and pinion mechanism similar to that described in the embodiment depicted in FIGS. 7-18. Feet 330, 332 for contacting and bracing against the sacrum 108, are illustrated in FIG. 20. A second adjustable spinal implant 400 comprises a second implantable actuator 404 coupled to a second adjustable element 406. A clamping bone anchor 494 holds outer diameter of the second implantable actuator 404. A left transverse process hook 424 is hooked around the left transverse process 180. In some embodiments, a stability element 313 may also be used with the left transverse process hook 424 (in the same manner as described with respect to the right transverse process hook 322), though it is not shown in FIG. 19. The first adjustable spinal implant 300 and second adjustable spinal implant 400 have separate internal adjustment mechanisms, including radially-poled permanent magnets. Therefore, the two adjustable spinal implants 300 and 400 may be independently adjustable in relation to one another. This may aid in situations where the L5 vertebra 106 is rotated undesirably along the axis of the subject's torso. For example, the first adjustable spinal implant 300 may be adjusted differentially relative to the second adjustable spinal implant 400 in order to derotate a chosen amount. During implantation, the first adjustable spinal implant 300 and the second adjustable implant 400 may be implanted through the same incision or they may be implanted through different incisions.

FIG. 21 illustrates an external adjustment device 1180 which may be used to non-invasively adjust devices and systems described herein. The external adjustment device 1180 comprises a magnetic handpiece 1178, a control box 1176 and a power supply 1174. The control box 1176 includes a control panel 1182 having one or more controls (buttons, switches or tactile, motion, audio or light sensors) and a display 1184. The display 1184 may be visual, auditory, tactile, the like or some combination of the aforementioned features. The external adjustment device 1180 may contain software which allows programming by a physician, including the ability to lock a patient out from using the external adjustment device 1180, limit the amount of possible adjustment per day, per hour, etc.

FIG. 22 shows an exploded view of the magnetic handpiece 1178 of the external adjustment device 1180. There are two magnets 1186 that can have a cylindrical shape. The magnets 1186 may be made from rare earth magnets. The magnets 1186 may be bonded or otherwise secured within magnetic cups 1187. The magnetic cups 1187 can include shafts 1198 attached to a first magnet gear 1212 and second magnet gear 1214. The orientation of the poles of each the two magnets 1186 are substantially fixed with respect to each other through a gearing system including, for example, center gear 1210, which meshes with both first magnet gear 1212 and second magnet gear 1214).

The components of the magnetic handpiece 1178 may be held together between a magnet plate 1190 and a front plate 1192. Most of the components are protected by cover 1216. The magnets 1186 rotate within a static magnet cover 1188, so that the magnetic handpiece 1178 may be rested directly on the patient while not causing motion to the external surfaces of the patient. Prior to distraction of the adjustable spinal implant 200 using the external adjustment device 1180, the operator places the magnetic handpiece 1178 over the patient near the location of the radially-poled permanent magnet 202, for example, on the skin covering the dorsal portion of the sacrum 108. A magnet standoff 1194 interposed between the two magnets 1186 can contain a viewing window 1196, that may aid in placement. For instance, a mark made on the patient's skin at the appropriate location with an indelible marker may be viewed through the viewing window 1196. To use the external adjustment device 1180 to perform a distraction, an operator generally holds the magnetic handpiece 1178 by its handles 1200 and causes motor 1202 to drive in a first direction. The motor 1202 may have a gear box 1206 which can cause the rotational speed of an output gear 1204 to be different from the rotational speed of the motor 1202 (for example, a slower speed). The output gear 1204 can then turn a reduction gear 1208 meshing with center gear 1210, which can cause center gear 1210 to turn at a different rotational speed than the reduction gear 1208. The center gear 1210 can mesh with both the first magnet gear 1212 and the second magnet gear 1214 thereby turning them at the same rate. Depending on the portion of the body where the magnets 1186 of the external adjustment device 1180 are located, it may be desired that the rate of rotation of the magnets be controlled to minimize the resulting induced current density imparted by magnet 1186 and cylindrical magnet 1134 though the tissues and fluids of the body. In some embodiments, a magnet rotational speed of about 60 RPM or less is contemplated. In other embodiments, a magnet rotational speed of about 35 RPM or less may be used. At any time, the distraction may be lessened by causing the magnets to rotate in the opposite direction (e.g., by depressing retract switch 1230). If the patient feels significant pain, or numbness in the area holding the device, the magnitude of distraction may be decreased. The magnets 1186 of the magnetic handpiece can comprise one or more permanent magnets or one or more electromagnets. For example, one or more electromagnets can be configured to provide a rotating magnetic field capable of causing rotation of the radially-poled permanent magnet 202.

FIGS. 23A through 23C illustrate a magnetic actuator 504 which may be used with any of the embodiments of the of devices as described and illustrated herein, and which allows for temporary or permanent removal of a rotatable magnetic assembly 542. Patients undergoing magnetic resonance imaging (MRI) may benefit from the removal of radially-poled permanent magnet 502 prior to MM in order to avoid a large imaging artifact caused by the radially-poled permanent magnet 502. Additionally, there is a risk that in implanted radially-poled permanent magnet 502 may be demagnetized upon entering an MM scanner. An actuator housing cap 588 has a male thread 599 which engages with a female thread 597 of the housing 505 of the magnetic actuator 504. Alternatively, a snap/unsnap interface may be used. A smooth diameter portion 595 of the actuator housing cap 588 is sealed with an o-ring 593, which is held within a circumferential groove on the inner surface of the housing 505. If, at a time subsequent to the implantation of the magnetic actuator 504, it is desirable to remove the rotatable magnetic assembly 542 while leaving the rest of the implant intact, a small incision may be made in the skin of a subject in proximity to the actuator housing cap 588, and the actuator housing cap 588 may be unscrewed. The rotatable magnetic assembly 542 may then be removed through the incision, as shown in FIG. 23A. FIGS. 23B and 23C show the subsequent steps of replacing the actuator housing cap 588 onto the housing 505 again sealing it against the o-ring 593. The incision may then be closed, and the subject may undergo typical MRI scanning. If desired, the rotatable magnetic assembly 542 may be replaced by following a reverse method.

FIGS. 24A through 24D illustrate a magnetic actuator 604 which may be used with any of the embodiments of the of devices as described and illustrated herein, and which allows for temporary or permanent removal of a radially-poled permanent magnet 602. An actuator housing cap 688 attaches to and detaches from the magnetic actuator 604 in the same manner as in the magnetic actuator 504 of FIGS. 23A through 23C. The radially-poled permanent magnet 602 has two radial portions 687 and two flat portions 685. The two flat portions 685 fit within flat walls 683 of a magnetic housing 640, which allows rotation of the radially-poled permanent magnet 602 to directly impart rotation on the magnetic housing 640 without the need for any adhesive or epoxy. A magnetic housing cap 681 having an o-ring 679 is attachable to and removable from the magnetic housing 640. If an MM of the subject is desired and it has been determined that the radially-poled permanent magnet 602 should be removed, a small incision may be made in the skin of the subject in close proximity to the actuator housing cap 688 through which the actuator housing cap 688 may be removed. The incision may be substantially at or near the location of an incision made during the implantation surgery, for example, adjacent or over the location of an incision made during the initial implantation surgery. Alternatively, the incision instead may be made in a separate location, as skin may be moved to access the magnetic actuator 604. Then magnetic housing cap 681 may then be removed from the magnetic housing 640. A pull rod 677 extends through a longitudinal hole (not shown) in the radially-poled permanent magnet 602, extending at one end such that it may be gripped, for example, by forceps or hemostats. The pull rod 677 has a flat base 675 at its opposite end so that, when pulled, it drags the radially-poled permanent magnet 602 with it. The radially-poled permanent magnet 602 may be removed, as shown in FIG. 24B (either permanently or temporarily) and the magnetic housing cap replaced (FIG. 24C). The actuator housing cap 688 may then be replaced (FIG. 24D). The incision may then be closed or allowed to close, and the subject may undergo typical MRI scanning. If desired, the radially-poled permanent magnet 602 may be replaced by following a reverse method. Alternatively, the magnetic housing cap 681 or the actuator housing cap 688 may be replaced by an alternatively shaped cap which will guide into a keyed structure within the magnet actuator 604 (not shown), thus keeping the internal mechanisms from turning, and keeping the subject's particular amount of adjustment from changing as the subject walks, runs and/or stretches.

When a desired magnitude of reduction has been reached—for example, lowering or maintaining the spondylolisthesis grade over a particular amount of time—any of the embodiments of the adjustable spinal implant disclosed herein may be removed from a patient. Alternatively, they may be left in place within a patient.

FIGS. 25 and 26 illustrate an adjustable spinal implant 700 according to another embodiment of the of devices as described and illustrated herein. The adjustable spinal implant 700 comprises an implantable actuator 704 having a transition section 701 which transitions to an adjustable element 706. Two feet 726 and 728 extending from the adjustable element 706 are configured to contact the medial surfaces 176 of the alas 166 of the sacrum 108. The implantable actuator 704 may have anchoring tabs 710 through which bone anchors 294 can be placed to secure the implantable actuator 704 to the sacrum 108. The adjustable element 706 features a tethering system for creating traction on the T5 vertebra 106. A right tether line 703 may be coupled to the right transverse process 178 of the L5 vertebra 106, and a left tether line 705 may be coupled to the left transverse process 180 of the L5 vertebra 106. The right tether line 703 and left tether line 705 are wrapped around each respective transverse process 178, 180 and secured to themselves via a crimp or clamp 723 and 725. This crimp or clamp 723 and 725 may be created using an appropriate tool during implantation, or may be pre-formed. In some embodiments, a durable surface 727 is wrapped around the transverse processes 178 and 180 first, in order to distribute contact stresses on the transverse processes 178 and 180.

The right tether line 703 and left tether line 705 enter the adjustable element 706 through a seal 734 (for example, an o-ring) which protects the inner contents of the adjustable element 706 from body fluids. The right and left tether lines 703 and 705 can wind first around first pulleys 751 and 753 and then around second pulleys 755 and 757 (which may be in an orthogonal plane to the first pulleys 751 and 753). The pulleys 751, 753, 755, and 757 may serve to guide the right and left tether lines 703, 705 towards the center of a cavity 717 in the adjustable spinal implant 700. In some embodiments, the right and left tether lines 703 and 705 bifurcate from single tether line 707 which extends over a main pulley 759 and is wound around a spool 709. In other embodiments, the right and left tether lines 703 and 705 themselves extend over a main pulley 759 and are then wound around a spool 709. The main pulley 759 can be held by post 763. The spool 709 can be rotationally held by a stepped post 721 having a large diameter portion 715 and a smaller diameter portion 713. The stepped post 721 is secured inside the adjustable spinal implant within the transition section 701 at a connection point 761. A radially-poled permanent magnet 702 is held within a magnetic housing 740 having a magnetic housing cap 744. The magnetic housing 744 cap and magnetic housing 740 are rotatable within a radial bearing 748. This portion of the assembly is enclosed by an actuator housing cap 788 and o-ring 765. The radially-poled permanent magnet 702 and thus magnetic housing 740 are coupled to a first planetary gear stage 746, which is in turn coupled to a second planetary gear stage 747. The second planetary gear stage 747 may be coupled to the spool 709 by pin 711. A thrust bearing 750 axially engages the spool 709 at the opposite end of the rotatable components from the radial bearing 748. A guide loop 719 assures that the single tether line 707 is smoothly wound around the spool 709. When a moving magnetic field is applied to the radially-poled permanent magnet 702 (for example, by use of the external adjustment device 1180), the radially-poled permanent magnet 702 and magnetic housing 740 can be caused to rotate, making the first and second planetary gear stages 746 and 747 rotate (at different rotational speeds as determined by the respective gear ratios) and thereby rotating the spool and taking up some of the single tether line 707. As the right and left tether lines 703 and 705 are pulled, traction (by the changing of tension and/or length of one or more of the tether lines 707, 703, 705) may be applied to the right and left transverse processes 178, 180, reducing the L5 vertebra 106 with respect to the sacrum 108. Alternatively, each of the tether lines 703, 705 may be wound on its own spool/magnet assembly and thus be independently adjustable. For example, the right tether line 703 may extend from a first actuator and the left tether line 705 may extend form a second actuator, with the first actuator independently adjustable from the second actuator.

FIGS. 27-30 illustrate embodiments of a driving element alternative that may be used instead of a rotatable magnetic assembly as the driving element 242 of a non-invasively adjustable spinal implant. FIG. 27 illustrates a non-invasively adjustable spinal system 1300 comprising an implant 1306 having a first implant portion 1302 and a second implant portion 1304, the second implant portion 1304 non-invasively displaceable with relation to the first implant portion 1302. The first implant portion 1302 is secured to a first bone portion 197 and the second implant portion 1304 is secured to a second bone portion 199 within a patient 191. A motor 1308 is operable to cause the first implant portion 1302 and the second implant portion 1304 to displace relative to one another. An external adjustment device 1310 has a control panel 1312 for input by an operator, a display 1314 and a transmitter 1316. The transmitter 1316 sends a control signal 1318 through the skin 195 of the patient 191 to an implanted receiver 1320. Implanted receiver 1320 communicates with the motor 1308 via a conductor 1322. The motor 1308 may be powered by an implantable battery, or may be powered or charged by inductive coupling.

FIG. 28 illustrates a non-invasively adjustable spinal system 1400 comprising an implant 1406 having a first implant portion 1402 and a second implant portion 1404, the second implant portion 1404 non-invasively displaceable with relation to the first implant portion 1402. The first implant portion 1402 is secured to a first bone portion 197 and the second implant portion 1404 is secured to a second bone portion 199 within a patient 191. An ultrasonic motor 1408 is operable to cause the first implant portion 1402 and the second implant portion 1404 to displace relative to one another. An external adjustment device 1410 has a control panel 1412 for input by an operator, a display 1414 and an ultrasonic transducer 1416, which is coupled to the skin 195 of the patient 191. The ultrasonic transducer 1416 produces ultrasonic waves 1418 which pass through the skin 195 of the patient 191 and operate the ultrasonic motor 1408.

FIG. 29 illustrates a non-invasively adjustable spinal system 1700 comprising an implant 1706 having a first implant portion 1702 and a second implant portion 1704, the second implant portion 1704 non-invasively displaceable with relation to the first implant portion 1702. The first implant portion 1702 is secured to a first bone portion 197 and the second implant portion 1704 is secured to a second bone portion 199 within a patient 191. A shape memory actuator 1708 is operable to cause the first implant portion 1702 and the second implant portion 1704 to displace relative to one another. An external adjustment device 1710 has a control panel 1712 for input by an operator, a display 1714 and a transmitter 1716. The transmitter 1716 sends a control signal 1718 through the skin 195 of the patient 191 to an implanted receiver 1720. Implanted receiver 1720 communicates with the shape memory actuator 1708 via a conductor 1722. The shape memory actuator 1708 may be powered by an implantable battery, or may be powered or charged by inductive coupling.

FIG. 30 illustrates a non-invasively adjustable spinal system 1800 comprising an implant 1806 having a first implant portion 1802 and a second implant portion 1804, the second implant portion 1804 non-invasively displaceable with relation to the first implant portion 1802. The first implant portion 1802 is secured to a first bone portion 197 and the second implant portion 1804 is secured to a second bone portion 199 within a patient 191. A hydraulic pump 1808 is operable to cause the first implant portion 1802 and the second implant portion 1804 to displace relative to one another. An external adjustment device 1810 has a control panel 1812 for input by an operator, a display 1814 and a transmitter 1816. The transmitter 1816 sends a control signal 1818 through the skin 195 of the patient 191 to an implanted receiver 1820. Implanted receiver 1820 communicates with the hydraulic pump 1808 via a conductor 1822. The hydraulic pump 1808 may be powered by an implantable battery, or may be powered or charged by inductive coupling. The hydraulic pump 1808 may alternatively be replaced by a pneumatic pump.

While embodiments of the present invention have been shown and described, various modifications may be made without departing from the scope of the present invention. Supplementation (graft) may be applied during the initial implantation of an embodiment of the adjustable spinal implant, and the adjustments may be made during the time period that the fusion is occurring, for example, less than six months, or more specifically, less than three months. This may, for example, include fusion being attempted between L5 106 and S1 122. The treatment of the patient may be to reduce the grade of spondylolisthesis, as described, but in certain cases, the goal may be simply to maintain the grade of spondylolisthesis in an otherwise progressing patient; for example, to keep spondyloptosis from occurring. In subjects who have undersized transverse processes, some augmentation of the transverse processes may be done prior to securing one of the embodiments of the present invention. In some cases, pedicle screws may be used instead of or to augment the connection to the transverse processes. An additional fulcrum may be placed between the vertebrae being treated (e.g., a wedge implant) in order to aid the derotation. The embodiments of the present invention may also be used in conditions other than spondylolisthesis, for example, ankylosing spondylitis. The invention, therefore, should not be limited, except to the following claims, and their equivalents.

It is contemplated that various combinations or subcombinations of the specific features and aspects of the embodiments disclosed above may be made and still fall within one or more of the inventions. Further, the disclosure herein of any particular feature, aspect, method, property, characteristic, quality, attribute, element, or the like in connection with an embodiment can be used in all other embodiments set forth herein. Accordingly, it should be understood that various features and aspects of the disclosed embodiments can be combined with or substituted for one another in order to form varying modes of the disclosed inventions. Thus, it is intended that the scope of the present inventions herein disclosed should not be limited by the particular disclosed embodiments described above. Moreover, while the invention is susceptible to various modifications, and alternative forms, specific examples thereof have been shown in the drawings and are herein described in detail. It should be understood, however, that the invention is not to be limited to the particular forms or methods disclosed, but to the contrary, the invention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the various embodiments described and the appended claims. Any methods disclosed herein need not be performed in the order recited. The methods disclosed herein include certain actions taken by a practitioner; however, they can also include any third-party instruction of those actions, either expressly or by implication. For example, actions such as “securing at least a portion of the non-invasively adjustable implant to a portion of the sacrum of the subject” include “instructing the securing at least a portion of the non-invasively adjustable implant to a portion of the sacrum of the subject.” The ranges disclosed herein also encompass any and all overlap, sub-ranges, and combinations thereof. Language such as “up to,” “at least,” “greater than,” “less than,” “between,” and the like includes the number recited. Numbers preceded by a term such as “approximately”, “about”, and “substantially” as used herein include the recited numbers, and also represent an amount close to the stated amount that still performs a desired function or achieves a desired result. For example, the terms “approximately”, “about”, and “substantially” may refer to an amount that is within less than 10% of, within less than 5% of, within less than 1% of, within less than 0.1% of, and within less than 0.01% of the stated amount. 

What is claimed is:
 1. A non-invasively adjustable spinal system, comprising: an actuator configured for remote activation, the actuator having: at least one anchoring structure configured to facilitate securement of the actuator to a portion of a sacrum; and a driving element; and an adjustment element configured to be coupled to the actuator, the adjustment element having an engagement structure configured to engage at least one transverse process of a lumbar vertebra, wherein remote activation of the driving element of the actuator causes movement of the adjustment element relative to the implantable actuator.
 2. The non-invasively adjustable spinal implant of claim 1, wherein the engagement structure is configured to engage at least one transverse process of an L5 lumbar vertebra.
 3. The non-invasively adjustable spinal system of claim 1, wherein the engagement structure is configured to engage both transverse processes of a lumbar vertebra.
 4. The non-invasively adjustable spinal system of claim 3, wherein the engagement structure includes a cross bar having a left transverse process hook and a right transverse process hook.
 5. The non-invasively adjustable of claim 1, wherein the driving element is selected from the group consisting of: a permanent magnet, an inductively coupled motor, an ultrasonically actuated motor, a subcutaneous hydraulic pump, a subcutaneous pneumatic pump, and a shape-memory driven actuator.
 6. The non-invasively adjustable spinal system of claim 5, wherein the driving element includes a radially-poled permanent magnet configured for rotation within the actuator.
 7. The non-invasively adjustable spinal system of claim 6, wherein the radially-poled permanent magnet is configured to be rotated by application of a rotating magnetic field.
 8. The non-invasively adjustable spinal system of claim 6, wherein the radially-poled permanent magnet is removable from the actuator.
 9. The non-invasively adjustable spinal system of claim 6, further comprising: an external adjustment device configured to produce a rotating magnetic field capable of rotating the radially-poled permanent magnet.
 10. The non-invasively adjustable spinal system of claim 9, further comprising at least one electromagnet.
 11. The non-invasively adjustable spinal system of claim 1, further comprising: a plurality of feet disposed on the adjustment element, each of the plurality of feet configured to extend between the adjustment element and the sacrum and configured to stabilize the adjustment element with respect to the sacrum.
 12. The non-invasively adjustable spinal system of claim 1, further comprising: a second actuator; a first transverse process hook coupled to the actuator; and a second transverse process hook coupled to the second actuator.
 13. The non-invasively adjustable spinal system of claim 12, wherein the actuator is independently adjustable from the second actuator.
 14. The non-invasively adjustable spinal system of claim 1, wherein the adjustment element includes a traction element.
 15. The non-invasively adjustable spinal system of claim 14, wherein the traction element includes a tether.
 16. The non-invasively adjustable spinal system of claim 15, wherein the actuator includes a rotatable spool configured to wind the tether, thereby changing at least one of the tension or the effective length of the tether.
 17. The non-invasively adjustable spinal system of claim 1, wherein the adjustment element is configured to move in an arcuate path.
 18. The non-invasively adjustable spinal system of claim 1, wherein the adjustment element includes a rack configured to be moved by a pinion.
 19. The non-invasively adjustable spinal system of claim 18, wherein the rack has an arcuate shape.
 20. The non-invasively adjustable spinal system of claim 1, wherein the adjustment element includes at least one gear operably coupled to an output shaft of the actuator. 